Methods and systems for the treatment of glaucoma using visible and infrared ultrashort laser pulses

ABSTRACT

Transcorneal and fiberoptic laser delivery systems and methods for the treatment of eye diseases wherein energy is delivered by wavelengths transparent to the cornea to effect target tissues in the eye for the control of intraocular pressure in diseases such as glaucoma by delivery systems both external to and within ocular tissues. External delivery may be affected under gonioscopic control. Internal delivery may be controlled endoscopically or fiberoptically, both systems utilizing femtosecond laser energy to excise ocular tissue. The femtosecond light energy is delivered to the target tissues to be treated to effect precisely controlled photodisruption to enable portals for the outflow of aqueous fluid in the case of glaucoma in a manner which minimizes target tissue healing responses, inflammation and scarring.

RELATED APPLICATIONS

This application is a continuation of U.S. Pat. Application No. 18/045,229, filed Oct. 10, 2022, which is a continuation of U.S. Pat. Application No. 17/302,965, filed May 17, 2021, now U.S. Pat. No. 11,510,813, issued Nov. 29, 2022, which is a continuation of U.S. Pat. Application No. 16/881,934, filed May 22, 2020, now U.S. Pat. No. 11,039,958, issued Jun. 22, 2021, which is a continuation of U.S. Pat. Application No. 16/008,917, filed Jun. 14, 2018, now U.S. Pat. No. 10,765,559, issued Sep. 8, 2020, which is a continuation of U.S. Pat. Application No. 14/732,627, filed Jun. 5, 2015, now U.S. Pat. No. 10,064,757, issued Sep. 4, 2018, which is a continuation of U.S. Pat. Application No. 13/464,949, filed May 4, 2012, which claims the benefit under 35 U.S.C. § 119(e) of U.S. Provisional Application No. 61/482,824, filed May 5, 2011, each of which are hereby incorporated by reference in their entireties.

BACKGROUND

Field of the Invention. The present invention pertains generally to methods and procedures for use in ophthalmic surgery. More particularly, the present invention pertains to the use of laser devises for photodisruption of tissue in the eye. The present invention is particularly, but not exclusively, useful for an ophthalmic surgical procedure involving transcorneal or fiberoptic photodisruption of tissue of the corneo scleral angle as a treatment for glaucoma.

Background of the Invention. Glaucoma refers to a series of relatively common eye disorders in which pressure within the eye is sufficiently high as to result in damage to sensitive intraocular structures, including the retina and optic nerve. Glaucomas are classified as primary (including chronic open angle glaucoma, angle closure glaucoma, mixed mechanism glaucoma and infantile glaucoma and secondary (related to other diseases of the eye). The elevation of intraocular pressure ultimately leads to irreversible destruction of the optic nerve. The clinical symptoms, which are not readily recognized in the early stages, are characterized mainly by a slow, relentless, progressive narrowing of the field of vision, and decrement in visual integration processing, including diminished dark adaptation. In the absence of treatment, the eventual outcome is total loss of vision often accompanied by severe eye pain.

In order to fully appreciate the described embodiments, a brief overview of the anatomy of the eye is provided. As schematically shown in FIG. 1 , the outer layer of the eye includes a sclera 17 that serves as a supporting framework for the eye. The front of the sclera includes a cornea 15, a transparent tissue that enables light to enter the eye. An anterior chamber 7 is located between the cornea 15 and the crystalline lens 4. The anterior chamber 7 contains a constantly flowing clear fluid called aqueous humor 1. The crystalline lens 4 is connected to the eye by fiber zonules, which are connected to the cilliary body 3. In the anterior chamber 7, an iris 19 encircles the outer perimeter of the lens 4 and includes a pupil 5 at its center. The diameter of the pupil 5 controls the amount of light passing through the lens 4 to the retina 8. A posterior chamber 2 is located between the crystalline lens 4 and the retina 8.

As shown in FIG. 2 , the anatomy of the eye also includes a trabecular meshwork 9, a narrow band of spongy tissue within the eye that encircles the iris 19. The trabecular meshwork (“TM”) varies in shape and is microscopic in size. It is generally triangular in cross-section, varying in thickness from about 100 µm to 200 µm. It is made up of different fibrous layers, having micro-sized pores forming fluid pathways for the egress of aqueous humor from the anterior chamber. The trabecular meshwork 9 has been measured to a thickness of about 100 µm at its anterior edge, Schwalbe’s line, 18 at the approximate juncture of cornea 15 and sclera 17.

The trabecular meshwork widens to about 200 µm at its base where it and the iris 19 attach to the scleral spur. The passageway through the pores in the trabecular meshwork 9 lead through a very thin, porous tissue called the juxtacanalicular trabecular meshwork 13, which in turn abuts the interior side of a structure called Schlemm’s canal 11. Schlemm’s canal 11 is filled with a mixture of aqueous humor and blood components and branches off into collector channels 12 that drain the aqueous humor into the venous system. Because aqueous humor is continuously produced by the eye, any obstruction in the trabecular meshwork, the juxtacanalicular trabecular meshwork or Schlemm’s canal, prevents the aqueous humor from readily escaping from the anterior chamber. This results in an elevation of intraocular pressure in the eye. Increased intraocular pressure can lead to damage of the optic nerve and eventual blindness.

Present surgical techniques to lower intraocular pressure include procedures enabling fluid to drain from within the eye to extra ocular sites. However, these drainage or “filtering” procedures not only increase the risk of causing a lens cataract, but often fail by virtue of their closure resulting from the healing of the very wound created for gaining access to the surgical site. Ab inferno surgical procedures, also, if not adequately stealth eventually fail. In creating the egress by photoablation or by photodisruption less inflammation at the egress site is induced than by current techniques, thus prolonging filtration wound function.

Lasers were first used in 1965 to repair retinal detachments. The procedure involved chorioretinal coagulation in which a laser beam positioned from without the eye was used to achieve fusion of the retina and the choroid. The technique consisted of introducing a laser beam from outside the cornea, and by employing the refractive media of the eye itself, the laser radiation was directed in such a manner that it was concentrated at a selected point upon the retina/choroid so that the tissues in a very localized area were photothermally congealed.

In contrast to thermal energy produced by visible and by infrared lasers, such as Nd:YAG systems, the high photon energies of femtosecond lasers can photodisrupt the material in question, namely eye tissue, in a manner which does not cause significant target tissue temperature elevation. By photodisruption, both visible and infrared femtosecond laser radiation can be used to drastically alter the target tissue in a “cold” environment. This becomes significant for controlled removal of organic substances, such as living tissue, in contradistinction to treatments in which heat is generated, e.g. by thermal lasers, which could damage, if not destroy, delicate eye tissue adjacent to the target sites to be removed and thereby induce healing responses.

Femtosecond (“FS”) lasers used for this purpose include the group of rapidly pulsed lasers which emit at 0.4 to 2.5 µm in the visible and infrared spectra. In contrast to the thermal visible and infrared radiation from some Nd:YAG or CO₂ lasers or the like, the high energy photons from femtosecond lasers at photodisruptive fluence levels are absorbed by the target tissues. This absorption creates a hot plasma at the focus, vaporizing tissue. The plasma subsequently expands supersonically launching a pressure wave. Later, a cavitation bubble forms and eventually collapses. The extent of the tissue damage caused by the pressure wave and cavitation bubble expansion is energy-dependent. Femtosecond pulses deposit very little energy while still causing breakdown, therefore producing surgical photodisruption while minimizing collateral damage.

Juhasz T, Chai D, Chaudhary G, et al.; Application of Femtosecond Laser Surgery for the Treatment of Glaucoma; in Frontiers in Optics, OSA Technical Digest (CD) (Optical Society of America, 2008) disclosed that FS laser pulses could be used to create partial thickness scleral channels that drain aqueous humor into the sub-conjunctiva! space, showing potential for the treatment of glaucoma. Toyran S, Liu Y, Singha S., et al.

Femtosecond laser photodisruption of human trabecular meshwork: an in vitro study; Exp. Eye Res. 2005; 81(3); 298-305, disclosed the use of FS lasers to perform photodisruption of human TM strips ex vivo, creating full-thickness ablation channels through the TM without collateral damage. The ideal settings for creating lesions with minimal collateral side effects on the inner surface of the TM are: Ti:Sapphire laser beam (45 fsec, 1 kHz, 800 nm) with 14.4 mJ pulse energy and an exposure time of 0.5 sec Nakamura H, Liu Y, Witt TE, et al.; Femtosecond laser photodisruption of primate trabecular meshwork: an ex vivo study; Invest. Ophthalmol. Vis. Sci. 2009; 1198-204 disclosed photodisruption by FS laser of the TM of ex vivo, intact, enucleated human and baboon eyes. The settings were 45 fsec, 1 kHz, 800 nm with 60 to 480 µJ and 0.001 to 0.3 sec exposure time. The study showed that laser ablation of the TM ab interno in ex vivo primate eyes is feasible by a custom femtosecond laser ablation system with a gonioscopic lens. The photodisruption did not reach Schlemm’s canal, although this goal could easily be achieved through an alteration in laser settings and delivery methods.

However, successful use of ultrashort laser pulses, such as those produced by a FS laser, in vivo to produce channels in the TM to relieve glaucoma has not been demonstrated by the work discussed above and presents challenges not present in those experimental studies. In particular, the laser beam must be delivered to a precise location on the TM in such a way as to avoid damage to adjacent and intervening tissue. The challenges of delivering adequate photodisruptive energy in precise patterns in shapes and depths include (a) the curved surface of the target, (b) the target lies beyond the critical angle of visible ocular structures seen through the cornea unaided, (c) optical coupling systems are necessary to visualize and target the intended treatment sites, e.g. trabecular meshwork and Schlemm’s canal, (d) the location of Schlemm’s canal may be difficult to establish particularly as it lies behind the optically significant trabecular meshwork, (e) once the inner wall of Schlemm’s canal therefore the “blood aqueous bather”, is penetrated, blood components may obscure the optical pathway for any future optical viewing and/or treating beams.

SUMMARY OF THE INVENTION

The present disclosure provides for the delivery of photodisruptive fluence levels of visible or infrared photons to the precise point of the target tissue of the eye by direct or fiberoptic delivery systems without impinging upon the overlying or surrounding tissue or upon the tissue at the region of beam entry into the eye for the purpose of effecting removal of select tissue in precise shapes and depths. Ultrashort laser pulses are directed into the eye either through the cornea or ab internally via fibers to enable laser radiation, including visible and infrared radiation, under gonioscopic control or through fiberoptic elements, including fiber lasers, thereby effecting precisely controlled photodisruptive removal of such target tissue of the corneo scleral angle. Such tissue may include TM, juxtacanalicular TM, and portions of Schlemm’s canal, collector channels, aqueous veins and sclera. Preferably, a laser with pulse duration in the range from 20 fs to 300 ps is used, although it is to be recognized that even shorter pulse durations may be used. The laser uses an optical coupling to affect controlled photodisruption of the target.

It is to be understood that this summary is provided as a means for generally determining what follows in the drawings and detailed description and is not intended to limit the scope of the invention. The foregoing and other objects, features and advantages of the invention will be readily understood upon consideration of the following detailed description taken in conjunction with the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

The foregoing summary of this disclosure as well as the following detailed descriptions of the embodiments is further understood when read in conjunction with the accompanying drawings, which are included by way of example, and not by way of limitation with regard to this disclosure.

FIG. 1 is a schematic sectional view of an eye illustrating the interior anatomical structure.

FIG. 2 is a perspective fragmentary view of the anatomy within the anterior chamber of an eye, depicting the corneoscleral angle.

FIG. 3 is a schematic sectional view of an eye illustrating a fiber-optic probe disposed next to the trabecular meshwork in the anterior chamber of the eye.

FIG. 4 is a schematic sectional view of an eye with an attached indirect goniolens with an interior mirror. The goniolens is attached to the cornea via suction or mechanical devices.

FIG. 5 is a schematic sectional view of an eye with an attached direct goniolens with an external mirror system. The mirror and lens are attached via retaining systems to the sclera.

FIG. 6 is a schematic sectional view of an eye with an attached indirect goniolens with an interior mirror. The goniolens is attached to the sclera via suction or mechanical devices.

FIG. 7 is a fragmentary cross section of the anatomy within the anterior chamber of an eye, showing a segment of target tissue to be photodisrupted.

DETAILED DESCRIPTION

The present disclosure provides for the delivery of photodisruptive fluence levels of visible or infrared photons to the precise point of the target tissue of the eye by direct or fiberoptic delivery systems without impinging upon the overlying or surrounding tissue or upon the tissue at the region of beam entry into the eye for the purpose of effecting removal of select tissue in precise shapes and depths. Ultrashort laser pulses are directed into the eye either through the cornea or ab internally via fibers to enable laser radiation, including visible and infrared radiation, under gonioscopic control or through fiberoptic elements, including fiber lasers, thereby effecting precisely controlled photodisruptive removal of such target tissue of the corneo scleral angle. Such tissue may include TM, juxtacanalicular TM, and portions of Schlemm’s canal, collector channels, aqueous veins and sclera. Preferably, a laser with pulse duration in the range from 20 fs to 300 ps is used, although it is to be recognized that even shorter pulse durations may be used. The laser uses an optical coupling to affect controlled photodisruption of the target.

A coupling system employs a goniolens or an ab interno fiberoptic that precisely targets the outflow obstructing tissues to effect removal of the outflow obstruction. Such targeting may include localization of Schlemm’s canal, detected optically or otherwise, such as by OCT (optical coherence tomography) or photoaccoustic spectroscopy.

The optical system may also include features to enhance visualization of Schlemm’s canal by controlling localized and diffuse pressure gradients, for example by creating relative hypotomy to induce blood reflux into Schlemm’s canal. Means of coupling the globe of the eye optically to the laser beam delivery system may be included to enable the exquisite precision of the photodisruptive laser. Such systems include goniolens flange systems, including coupling capabilities such as suction, with diameters in the range of IO to 25 mm, fluidic chambers both to control intraocular pressure (“IOP”) and to maintain corneal clarity and shape. To enable optical pathways, such as planar surface to enable precision targeting, suction means for similar purposes which, in addition, exquisitely control light energy delivery registration to the target tissues. In the case of the fiber laser, the fiber may have multiple channels to control intraocular pressure, to enable visualization and optical coupling to Schlemm’s canal.

Preferably, the procedure for creating openings in the trabecular meshwork comprises:

(1) imaging the target tissue, (2) locking a pattern to the image, (3) creating the pattern and controlling the depth of laser penetration, and (4) maintaining IOP to enable visualization of Schlemm’s canal and concurrently controlling egress of blood to prevent optical decoupling of light obstruction for subsequent laser delivery to target tissue.

Several 20 to 200 µm partial depth openings may be created concurrently without complete penetration to prevent blood reflux or other optical pathway obscuring elements after which Schlemm’s canal inner wall penetration is effected to all sites concurrently.

IOP is altered to affect this optical pathway, which is lowered to allow targeting of Schlemm’s canal then elevated to prevent blood reflux.

Gonioscopic an fiberoptic delivery systems for laser surgery in the eye wherein thermal and/or radiation damage to the eye is minimized are disclosed.

In connection with glaucoma treatment, laser energy is applied gonioscopicay transcorneal or directed through the fiberoptic element. When gonioscopic, the deflecting mirror may be stationary or may have elements to adjust the mirror within the goniolens delivery system both to precisely target the subject tissue and to precisely direct femtosecond laser energy to these tissues. Such a mirror may be mechanically controllable to effect scanning. The gonioscope is coupled to the eye by various means, including prongs, clips, suction, viscoelastic, aqueous solution and inflatable balloons. The laser delivery system is also coupled both to the goniolens and via the goniolens to the target cornea-scleral angle tissues. The optical delivery is stabilized through precise control of the goniolens and goniolens mirror position and control of the femtosecond laser energy delivered to the target tissue by sensors which detect precise laser tissue interactions as they occur.

The systems may include image stabilization to enable precise laser coupling to the docked goniolens device which includes a mirroring/light deflecting system to enable viewing and treating the cameo scleral angle structure at the laser delivery system, at the goniolens or fiber or both.

In one embodiment a goniolens is applied to the cornea and a laser beam is focused on the target tissue. In another embodiment, a fiberoptic handpiece is passed through an incision in the eye where it is stabilized and secured to the globe and the laser beam is focused on the target tissue.

In one goniolens configuration, a multidimensional mobile reflective surface (e.g., a Mylar balloon) is moved (horizontally, vertical and in depth) by inflation or deflation. This system can include fluidics to control temperature within the lens system. This configuration also may include concurrent illuminating beams and treatment beams with image capture for pixel to pixel image matching to control precise targeting when coupled to a mobile or curved target.

In another goniolens configuration DLP (Digital Light Processing) optical semiconductors or equivalent are used to control the gonioscopic delivery.

In yet another configuration, the system is capable of detecting cardiac cycle pulsation and the filling and emptying causing choroid translation of outflow structures by optical or ultrasound techniques, coupling the detection system to the optical delivery system to enable precise photo disruption of target tissue by means of a combination or individually: (a) mechanically controlled mirror, (b) piezoelectric controlled mirror, (c) DLP optical semiconductor, (d) surface reflecting fluid balloons (e.g. Mylar) included at the laser and/or within a gonioscopic delivery system.

The goniolens air/surface optics are either plano or concave or convex. The mirror/light reflecting element optics are either plano, concave, convex, complex curved or in a segmented mirror array. Light altering materials include variable optical density fluid lair filled balloons, glass, plastic or metal shaped to enable photodisruption to occur at target regions which are both beyond the critical angle to the corneal surface and are curved, residing on the inner surface of a globe.

The laser beam emitted from the laser source may be parallel, convergent or divergent and it is altered by the lens mirror system to enable all forms of emitted beams to focus with a suprathreshold photodisruptive fluence at the target tissue.

In one configuration, the goniolens includes a pressure detection means to compensate for cardiac cycle translation of the entire globe/orbit structures/choroid and intraocular structures including detection of choroidal filling and emptying from cardiac cycle events, which may include pressure detectors in the goniolens or goniolens flange and software in the laser delivery system to compensate for this target translation to enable precise target photodisruption on the moving target.

A concentric ring system may be used to enable (1) registration either through suction or through a retaining mechanical device (prongs, corkscrew) (2) IOP control (3) ocular pulsation detection.

A bladder/balloon system may be used to control optical surfaces, including cornea and any internal mirroring surfaces to enable an emitter to best couple to the target tissue. In coupling the cornea, the cornea may be compressed (e.g. flattened) or the goniolens corneal surface may be curved and coupled to the corneal surface by optically neutral fluidic means, liquids and gels.

In the case of a direct (e.g. non mirror) goniolens delivery system the direct goniolens is retained in a holding device coupled to an optic delivery system with mirror external to the goniolens. Such external mirroring enables the laser source and viewing optics to be inclined at angles from 10° to 170°, often 60° to 120° and most often 80° to 110° in relation to the target tissue.

In the moving eye/goniolens complex the laser fires only when the target is optically captured and stabilized. These optical coupling mechanisms enable precise photodisruption at the target tissue in space and in depth.

In the case of an ab interno fiber, the optical delivery is stabilized through precise control of the fiber position and control of the femtosecond laser energy delivered from the fiber tip by sensors which detect precise fiber tip position and alignment to the target tissue.

The photodisruptive radiation is directed to the target tissues, namely corneoscleral angle structures comprising trabecular meshwork, juxtacanalicular trabecular meshwork, components of Schlemm’s canal, and in some cases adjacent cornea, sclera, and iris structures to create fluid passageways between the anterior chamber of the eye and Schlemm’s canal or alternatively the suprascleral/subTenon space or alternatively the suprachoroidal space.

Photodisruptive laser energy is targeted to gonioscleral angle structures for the purpose of removing tissue which impedes aqueous outflow or to redirect outflow. Openings are created by patterns of adjacent photodisruption regions in this tissue. The patterns consist of various shapes in size ranging from surface dimensions of 20 to 200 microns and depth adequate to penetrate the inner wall of Schlemm’s canal. Patterning enables openings to be created individually, sequentially or several concurrently. In one iteration, when concurrently, the depth is controlled at each opening to allow the creation of craters without entering SC until all craters are at a depth after which minimal additional tissue removal would enter SC thus enabling the optical pathway in the anterior chamber to remain clear. Only at this time would SC be perforated at each crater concurrently to minimize optical pathway obscuration by blood reflux from SC.

In other iterations, in which the IOP is regulated to prevent blood reflux from SC, other patterning options are used, to create individual openings or several concurrent openings in from 1 to 12 clock hours of the angle.

Surgical trauma to the outer wall of Schlemm’s canal, or in the case of full thickness penetration to the overlying conjunctiva! and Tenon’s tissue, all extremely subject to scarring, is thereby minimized. This is in contrast to current procedures which result in more scarring of sensitive ocular structures and therefore more rapid failure of procedures whose purpose is to control IOP.

By minimizing trauma while creating an aqueous humor egress route, the present invention minimizes healing and increases longevity of improved outflow at the site of filtration. The present invention enables a significantly greater opportunity for success, including the ability to titrate the amount of photodisruptive energy necessary to result in a measured lowering of intraocular pressure.

Referring to FIG. 6 , an overview of a method of operating a fiber-optic laser delivery system for treatment of glaucoma or other eye conditions follows: FIG. 6 is a side sectional view of the interior anatomy of a human eye showing fiber-optic probe 23 in relation to an embodiment of a method of treating glaucoma. After applying local and/or peri retrobular anesthesia, a small self-sealing incision 14 can be created in the cornea 15 with a surgical blade or femtosecond laser or other device. The anterior chamber can be further stabilized with a viscoelastic agent. Fiber optic probe 23 can then be positioned and advanced in the incision.14 into the anterior chamber 7 to target the trabecular meshwork immediately or ab interno or a distal end of fiber-optic probe 23 contacts or is substantially adjacent to the target tissue for removal. Fiber optic probe 23 may be manually directed or held rigid in relation to the ocular structures via anchoring to the globe, sclera 17 or cornea 15 through devices which may include prongs 56 which also may hold in place a pressure regulating system 55 and an ocular pulse sensing system 54.

Laser energy is delivered from the distal end of fiber-optic probe 23 targeting the trabecular meshwork across the anterior chamber or in contact or adjacent to the tissues sufficient to cause photodisruption. Tissues to be removed include the trabecular meshwork 9, the juxtacanalicular trabecular meshwork 13 and an inner wall of Schlemm’s canal 11. Fiber-optic probe 23 delivered photodisruptive energy creates an aperture in the proximal inner wall of Schlemm’s canal 11 but does not perforate the distal outer wall. In some embodiments, additional apertures can be created in the trabecular meshwork and the target tissue following reposition of the probe. Thus by removing outflow obstructing tissues, the resultant aperture or apertures are effective to restore relatively normal rates of drainage of aqueous humor.

Referring to FIGS. 3-5 , an overview of a method of surgical gonioscopic delivery systems for the treatment of glaucoma or other eye conditions follows: FIG. 3 shows an optical delivery system consisting of an indirect goniolens 50 attached to the sclera 17 mechanically or by prongs 56 or suction, with an internal mirror 52. The mirror may be individual or segmented and fixed or mobile to enable scanning for both viewing and for treatment targeting. In the condition of a mobile mirror/mirror surface, the mirror 52 can be controlled mechanically or pneumatically or with a Mylar type surface reflecting balloon. The mirror can be plano, concave, convex and singular or in a segmented array.

A beam 51 of pulsed radiation is generated by a femtosecond laser and delivered into the eye by the delivery system, including the goniolens 50. The beam 51 is reflected by a mirror 52 which may be controlled by a servo system 53 connected to a controller 58 to focus scanning photodisruptive energy onto the curved surface of the target tissue. The optics enable bidirectional use, one direction is used to treat the target tissue, the other direction is used to view and/or sense the x, y, z coordinates of the targeted tissue to enable precise treatment and removal of the target regions. The beam 51 has a set of pulse parameter ranges specifically selected to photodisrupt targeted tissue of the trabecular meshwork, while minimizing damage to surrounding tissue. Thus, the beam has a wavelength between 0.4 and 2.5 microns. The exact wavelength used for a particular subject depends on tradeoffs between strong absorption by the meshwork and transmission of preceding ocular structures and aqueous humor. FIG. 4 shows an indirect goniolens 50 attached to the cornea 15 mechanically 56 or by suction with an internal mirror 52. FIG. 5 shows a direct goniolens attached to the sclera 17 by suction 57 or mechanically with a mirror system 52 external to the goniolens.

The pulse duration of the laser beam is chosen to have a high probability of photodisrupting material of the corneoscleral angle outflow tissues. There is an inverse relationship between the laser pulse duration and the energy required in each pulse to generate optical breakdown. The pulse duration is selected to be shorter than the thermal relaxation of the target so that only the targeted material is heated, and the surrounding tissue is unaffected. Thus, the pulse duration is between 20 fs and 300 ps. The pulse rate is between 1 and 500 KHz.

The pulse energy is chosen to facilitate photodisruption and minimize the shockwave effect of the laser light. A typical value for the pulse energy is between 300 to 1500 nJ.

The spot diameter is chosen such that sufficient laser energy density is provided to facilitate photodisruption of the trabecular meshwork tissue. The spot size is between 1 to 10 microns.

The goniolens 50 is anchored either on the sclera 17 or the cornea 15 by a suction ring 57 or prongs 56. The anchoring system is attached to a pressure regulating system 55 and an ocular pulse sensing system 54. The anchoring system is either concentric 57 or segmented 56. Scanning the spot in the x, y, and z direction effects patterns for tissue removal.

FIG. 7 shows the target tissue to be photodisrupted in a perspective view 70 and in a cross-sectional view 71. In this case a single site is demonstrated but understood is duplication of this site over several regions individually or concurrently.

Alternatively, the TM may be approached ab externo via the semi-transparent sclera using high numerical aperture optics and a fundamental wavelength that allows deep penetration through the sclera. This produces targeted ablation of the deep corneo scleral angle structures, specifically targeting TM, JCTM and portions of Schlemm’s Canal. In this instance the coupling lens could be planar or curved.

All coupling lenses, goniolenses and fibers require focusing devices at the laser which couple optically to the lenses, goniolenses and fibers to effect appropriate fluences at the target tissue to effect micro ablations and thereby tissue removal.

Preferably, the procedure for ultrashort laser pulse trabeculostomy comprises the steps that follow.

1. Prepare patient for femto laser trabeculostomy procedure.

2. Prepare femto laser which has been pretested on a model of trabecular meshwork for accuracy and fluence at the target tissue.

3. Align gonio lens with optical alignment system of laser visualization system to target planned trabecular meshwork tissue sites and lock the target into the system for treatment.

4. In the case where the gonio lens mirror is not stationary, but mobile, assure the tracking system is engaged to control all optical surfaces.

5. Secure the gonio lens onto the eye. This may be pneumatic or physical engagement to control all movement and enable tracking system to engage and apply energy only when target is precisely focused for appropriate delivery of laser energy to the target sites. If mobile, laser will only engage when precise target alignment assures exact tissue targeting in x, y and z loci.

6. Anchor the gonio lens either on the cornea or the sclera either by prongs or a suction ring.

7. Attach anchoring system to a pressure regulating system and an ocular pulse sensing system.

8. In the ease where cardiac cyclic translation of target is monitored and controlled, engage this system to enable precise depth targeting.

9. Couple end of optical pathway to a fem to second laser.

10. Locate Schlemm’s canal with the gonioscope.

11. The goniolens mirror may be curved to allow targeting of curved trabecular meshwork.

12. Focus laser beam on target tissue.

13. Photodisrupt target tissue until crater forms adjacent to Schlemm’s canal.

14. Repeat step 14. up to 10 times in a pattern, for example, from 5 o′clock to 1 o′clock.

15. The patterns consist of various shapes in size ranging from surface dimensions of 20 to 200 microns and depth adequate to penetrate the inner wall of Schlemm’s canal.

16. Using the laser, concurrently extend craters so they become ostia into Schlemm’s canal.

17. Detach gonioscope.

18. In the case where femto laser energy is delivered fiberoptically within the eye, all above apply. In addition, following paracentesis and stabilization of the anterior chamber with aqueous and/or viscoelastic agents, the fiberoptic delivery system is placed into the anterior chamber and imaging of all relevant structures is performed to assure targeting to planned sites. The fiber and fiber position maintaining devices are engaged and enabled, manually and/or automatically.

The terms and expressions which have been employed in the foregoing specification are used therein as terms of description and not of limitation, and there is no intention, in the use of such terms and expressions, to exclude equivalents of the features shown and described or portions thereof, it being recognized that the scope of the invention is defined and limited only by the claims that follow. 

What is claimed is:
 1. A method of creating one or more openings in a trabecular meshwork of an eye of a patient to conduct fluid from an anterior channel into a Schlemm’s canal of the eye, comprising: ablating a first region to a first depth in the trabecular meshwork with first laser pulses; ablating a second region to a second depth in the trabecular meshwork with second laser pulses; and extending the first region with third laser pulses to a third depth and extending the second region with fourth laser pulses to a fourth depth, so as to form a channel between the Schlemm’s Canal and the trabecular meshwork to conduct fluid from the anterior channel into the Schlemm’s canal; wherein each of the laser pulses comprises a wavelength of within a range from 0.4 to 2.5 microns, a fluence level to produce optical breakdown, and a pulse duration in a range from 20 femtoseconds to 300 picoseconds.
 2. The method of claim 1, wherein the laser pulses are directed through a cornea of the eye to ablate the trabecular meshwork.
 3. The method of claim 1, wherein a gonioscopic lens is coupled to the eye and the laser pulses are transmitted through the gonioscopic lens.
 4. The method of claim 1, wherein the laser pulses are scanned in an ablation pattern comprising adjacent regions in the trabecular meshwork to form the one or more openings.
 5. The method of claim 1, wherein the laser pulses are reflected off a curved mirror and wherein the laser pulses are scanned and focused into a curved trabecular meshwork to form the one or more openings in the curved trabecular meshwork.
 6. The method of claim 1, wherein an intraocular pressure of the eye is lowered to allow targeting Schlemm’s canal and then elevated to prevent blood reflux.
 7. The method of claim 1, wherein Schlemm’s canal is detected optically or by optical coherence tomography (OCT) or by photoacoustic spectroscopy.
 8. The method of claim 1, wherein the laser pulses are directed through a sclera of the eye to ablate the trabecular meshwork.
 9. The method of claim 1, wherein at least a portion of the trabecular meshwork comprises a lattice structure having voids, and the channel results in fluid communication between the Schlemm’s Canal and one or more of the voids.
 10. An ophthalmic surgical system comprising: a first optical apparatus comprising: a patient interface comprising a lens with a concave surface, the patient interface configured to couple to a cornea of a patient at the concave surface; wherein the first optical apparatus is configured to receive a bidirectional beam and redirect the bidirectional beam through the cornea of the patient and toward a trabecular meshwork of an eye; a second optical apparatus optically coupled to the first optical apparatus, the second optical apparatus comprising: a laser source configured to deliver energy to the trabecular meshwork along a beam pathway; an imaging apparatus configured to view a surgical procedure at the trabecular meshwork along the beam pathway; and a bidirectional optic disposed to combine a first beam delivered by the laser source and a second beam associated with the imaging apparatus to form the bidirectional beam; wherein the laser source is configured with pulse parameters to selectively photodisrupt targeted tissue of the trabecular meshwork.
 11. The ophthalmic surgical system of claim 10, further comprising a mirror for redirecting the bidirectional beam to the lens.
 12. The ophthalmic surgical system of claim 11, further comprising a servo system coupled to the mirror and configured to change an orientation of the mirror to scan the bidirectional beam in two or more directions.
 13. The ophthalmic surgical system of claim 12, wherein the servo system is configured to focus the bidirectional beam onto a curved surface of the trabecular meshwork.
 14. The ophthalmic surgical system of claim 10, wherein the lens comprises a meniscus lens having a peripheral region and a central region and wherein the lens is thicker nearer the central region and thinner nearer the peripheral region.
 15. The ophthalmic surgical system of claim 10, wherein the lens comprises an indirect goniolens.
 16. The ophthalmic surgical system of claim 10, wherein the lens comprises the concave surface and an opposing lens surface and has a first refractive index change at the opposing lens surface from high to low, the first refractive index change configured to bend the bidirectional beam in a first direction.
 17. The ophthalmic surgical system of claim 16, further comprising a second optical interface between the concave surface of the lens and the cornea of the patient and further comprising a second refractive index change from low to high, the second refractive index change configured to bend the bidirectional beam in a second direction opposite the first direction.
 18. The ophthalmic surgical system of claim 10, wherein the patient interface comprises a suction ring configured to contact a sclera of the eye and establish an annular cavity.
 19. The ophthalmic surgical system of claim 18, wherein the patient interface comprises a source of vacuum in communication with the annular cavity and configured to draw a vacuum within the annular cavity and thereby adhere the suction ring to the cornea of the patient.
 20. The ophthalmic surgical system of claim 10, wherein the imaging apparatus comprises an optical coherence tomography device.
 21. The ophthalmic surgical system of claim 10, wherein the imaging apparatus comprises a source of illumination. 